Small diameter corneal inlays

ABSTRACT

Methods of implanting corneal inlays, such as small diameter corneal inlays. The inlays may be adapted to change the corneal surface curvature to provide central near vision and peripheral distance vision.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No.15/219,130, filed Jul. 25, 2016, which application is a continuation ofU.S. application Ser. No. 13/854,588, filed Apr. 1, 2013, now abandoned;which application is a continuation of U.S. application Ser. No.12/877,799, filed Sep. 8, 2010, now abandoned; which application is acontinuation-in-part of U.S. application Ser. No. 11/554,544, filed Oct.30, 2006, now U.S. Pat. No. 8,057,541, which claims the benefit ofProvisional Appln. No. 60/776,458, filed Feb. 24, 2006;

U.S. application Ser. No. 12/877,799, filed Sep. 8, 2010, is also acontinuation-in-part of U.S. application Ser. No. 12/418,325, filed Apr.3, 2009, now U.S. Pat. No. 8,900,296; which is a continuation-in-part ofU.S. application Ser. No. 11/738,349, filed Apr. 20, 2007, nowabandoned.

All of the aforementioned applications are incorporated by referenceherein.

INCORPORATION BY REFERENCE

All publications and patent applications mentioned in this specificationare herein incorporated by reference to the same extent as if eachindividual publication or patent application was specifically andindividually indicated to be incorporated by reference.

BACKGROUND OF THE INVENTION

Abnormalities in the human eye can lead to vision impairment. Sometypical abnormalities include variations in the shape of the eye, whichcan lead to myopia (near-sightedness), hyperopia (far-sightedness) andastigmatism as well as variations in the tissue present throughout theeye, such as a reduction in the elasticity of the lens, which can leadto presbyopia. A variety of technologies have been developed to try andaddress these abnormalities, including corneal implants.

Corneal implants can correct vision impairment by altering the shape ofthe cornea. Corneal implants can be classified as an onlay or an inlay.An onlay is generally considered an implant that is placed over thecornea such that the outer layer of the cornea, e.g., the epithelium,can grow over and encompass the implant. An inlay is generallyconsidered an implant that is implanted in the cornea beneath a portionof the corneal tissue by, for example, cutting a flap in the cornea andinserting the inlay beneath the flap. Because the cornea is thestrongest refracting optical element in the human ocular system,altering the cornea's anterior surface is a particularly useful methodfor correcting vision impairments caused by refractive errors. Inlaysare also useful for correcting other visual impairments includingpresbyopia.

SUMMARY OF THE INVENTION

The disclosure generally describes corneal inlays which are adapted tochange the shape of the cornea to provide central near vision zone and aperipheral distance vision zone in the cornea. In general, the inlay issized such that when positioned within the cornea, a central region ofthe cornea increases in curvature, thereby providing for near vision. Aregion peripheral to the central region provides for distance vision.

One aspect of the disclosure describes a corneal inlay comprising aninlay body having a diameter between about 1 mm and about 3 mm, whereinthe body has an index of refraction that is substantially the same as acornea. The inlay can have an index of refraction that is about 1.36 toabout 1.39.

In some embodiments the diameter of the inlay is about 2 mm.

In some embodiments the inlay body has a central thickness that is about20 microns to about 50 microns, and in some embodiments it is about 30microns.

In some embodiments the inlay has a peripheral edge thickness betweenabout 8 microns and about 15 microns, and in some embodiments is about12 microns.

In some embodiments the inlay body has an anterior radius of curvaturebetween about 7 mm and about 12 mm, and in some embodiments in about 10mm.

In some embodiments the inlay body has a posterior radius of curvaturebetween about 5 mm and about 10 mm, and in some embodiments is about 8.5mm.

BRIEF DESCRIPTION OF THE FIGURES

FIG. 1 is a cross-sectional view of a conventional implantable lens.

FIG. 2A is a perspective view depicting an example embodiment of animplantable lens.

FIG. 2B is a top-down view depicting another example embodiment of theimplantable lens.

FIGS. 2C, 2D and 2E are cross-sectional views taken along line 1-1 ofFIG. 2B depicting additional example embodiments of the implantablelens.

FIG. 3 is a cross-sectional view depicting an anterior portion of ahuman eye with an example embodiment of the lens implanted therein.

FIGS. 4, 5, 6, 7, 8 and 9 are cross-sectional views taken along line 1-1of FIG. 1B depicting additional example embodiments of the implantablelens.

FIG. 10A is a top-down view depicting another example embodiment of theimplantable lens.

FIG. 10B is a cross-sectional view taken along line 2-2 of FIG. 10Adepicting another example embodiment of the implantable lens.

FIG. 11A is a perspective view depicting another example embodiment ofthe implantable lens.

FIG. 11B is a top-down view depicting another example embodiment of theimplantable lens.

FIGS. 11C and 11D are cross-sectional views taken along line 3-3 of FIG.11B depicting additional example embodiments of the implantable lens.

FIGS. 12A, 12B, 12C and 12D are block diagrams depicting an examplemethod of manufacturing the implantable lens.

FIG. 13 is a cross-sectional view depicting another example embodimentof the implantable lens.

FIG. 14A is a top-down view depicting another example embodiment of theimplantable lens.

FIGS. 14B and 14C are cross-sectional views taken along line 4-4 of FIG.14A depicting additional example embodiments of the implantable lens.

FIG. 15 is a cross-sectional view of a cornea showing an intracornealinlay implanted in the cornea according to an embodiment of theinvention.

FIG. 16 is a diagram of an eye illustrating the use of a small diameterinlay to provide near vision according to an embodiment of theinvention.

FIG. 17 is a cross-sectional view of a cornea showing an inlay implantedin the cornea and a change in the anterior corneal surface induced bythe, inlay including a drape region according to an embodiment of theinvention.

FIG. 18 illustrates various possible shapes for the drape region.

FIG. 19 is a cross-sectional view of a cornea showing a thicknessprofile for providing a desired refractive correction according to anembodiment of the invention.

FIG. 20 is a 3D topographic difference map showing the change in theanterior corneal surface induced by an inlay according to an embodimentof the invention.

FIG. 21 shows an average radial elevation profile induced by an inlayaccording to an embodiment of the invention.

FIG. 22 shows a contour map of the refractive change induced by an inlayaccording to an embodiment of the invention.

DETAILED DESCRIPTION OF THE INVENTION

Some corneal implants that are relatively flat around the outer edges,such as aspherical implants and shallow spherical implants to name afew, can suffer from edge lift. Edge lift occurs when the anteriorsurface of the implant around the outer edge tends to curve or lift backtowards the apex. FIG. 1 is a cross-sectional view of a conventionalcorneal implant 20 suffering from edge lift, which is exaggerated forthe purposes of illustration. Here, the implant 20 has an outer edge 21,an anterior surface 22, an apex 23 and a posterior surface 24. An idealedge profile is indicated by dashed line 10. In the ideal case, the mostposterior point on the anterior surface 22 is located at the outer edge21. However, in a lens suffering from edge lift the most posterior pointof the anterior surface 22 can be located at a position 24 closer to theapex 23 than the outer edge 21. Edge lift can progress and build up overtime and result in deteriorated optical performance and can also makethe implantation procedure more difficult.

In some embodiments the inlays have modified edge regions that canreduce stimulation of adverse tissue reactions in proximity to the lens.FIGS. 2A-E depict various views of an example embodiment of implantablelens 100. FIG. 2A is a perspective view depicting implantable lens 100,where lens 100 has lens body 101, anterior surface 102, posteriorsurface 103 and outer edge surface 104. FIG. 2B is a top-down view oflens 100 taken in direction 110. Here it can be seen that lens body 101has a generally circular outer profile 119 with central apex 105representing the most anterior point of anterior surface 102. Diameter112 represents the overall diameter of lens body 101 and diameter 114represents the diameter of corrective portion 122, which is the portionof anterior surface 102 configured to provide correction for one or morespecific visual impairments.

FIG. 2C is a cross-sectional view of lens 100 taken along line 1-1 ofFIG. 2B. From this view it can be seen that anterior surface 102 issubstantially spherical with radius of curvature 106 measured fromvertex 108 located on central axis 118, which intersects apex 105.Likewise, posterior surface 103 also has its own radius of curvature 107measured from vertex 109. The corrective power of lens 100 is dependentupon these radii 106-107 and can be varied as desired by adjustment ofeither radii 106-107. It can also be seen here that lens 100 isconfigured to correct for hyperopia, i.e., the relation of anteriorsurface 102 to posterior surface 103 gives lens body 101 a convergingmeniscus-like shape along line 1-1. The thickness of lens body 101 alongcentral axis 118 is referenced as center thickness 140.

FIG. 2D is an enlarged cross-sectional view of lens 100, showing region111 of FIG. 2C in greater detail. In FIG. 2D, corrective portion 122 ofanterior surface 102 is substantially spherical and anterior surface 102also includes a beveled portion 124. Here, beveled portion 124 is curvedwith a single radius of curvature and is referred to as bevel radius124. As used herein, “bevel” is defined to include flat surfaces, curvedsurfaces and surfaces of any other shape. Bevel radius 124 abutsspherical portion 122 at interface 123. Adjacent to bevel radius 124 isouter edge surface 104, the abutment between bevel radius 124 and outeredge surface 104 being referenced as interface 125. Outer edge surface104 includes first portion 126 and second portion 128, which abut eachother at interface 127. Second edge surface portion 128 abuts posteriorsurface 103 at interface 129. Here, first edge surface portion 126 iscurved and is referred to as edge radius 126. In this embodiment, edgethickness 130 is defined as the height of second edge surface portion128 in the Z direction from the most posterior point of lens body 101(interface 129 in this instance) to interface 127.

FIG. 2E is another cross-sectional view of region 111 depicting theexample embodiment of FIG. 2D with edge radius slope angle 132, whichdefines the slope of edge radius 126. Edge radius slope angle 132 can bedefined as the angle between axes 131 and 133. Here, axis 131 isparallel to central axis 118 and intersects interface 125, while axis133 intersects interfaces 125 and 127. Also depicted here is bevelradius slope angle 135, which defines the slope of bevel radius 124.Bevel radius slope angle 135 can be defined as the angle between axes134 and 136. Here, axis 134 is parallel to central axis 118 andintersects interface 123 and axis 136 intersects interfaces 123 and 125.

As can be seen in FIGS. 2D-E, edge radius 126 preferably slopes in the−Z direction to a greater degree than bevel radius 124, so that edgeradius 126 converges towards posterior surface 103 at a greater ratethan bevel radius 124. Stated in terms of slope angles, edge radiusslope angle 132 is preferably smaller than bevel radius slope angle 135.As a result, lens 100 is less susceptible to edge lift. Also, thegradual transition between spherical portion 122 and posterior surface103 can reduce stimulation of adverse tissue reactions to lens 100.

For instance, FIG. 3 is a cross-sectional view depicting an anteriorportion of human eye 200 including lens 202, aqueous humor 203, ciliarybody 204, iris 205 and cornea 206 with an example embodiment of lens 100implanted therein. Here, lens 100 is shown implanted as a corneal inlayalthough, it should be noted that lens 100 can also be implanted as acorneal onlay in a position closer to the anterior surface of cornea206. The gradual transition in the edge region of lens 100 facilitatesthe acceptance of lens 100 by the surrounding corneal tissue 207, moreso than conventional lenses with an unbeveled sharp or steep transitionbetween the anterior and posterior surfaces. As a result, lens 100 isless susceptible to undesirable conditions such as corneal haze and thelike. In addition, during the implantation procedure, the modified edgeregion of lens 100 makes it easier to ascertain whether lens 100 isproperly oriented or whether lens 100 is inverted.

In order to sustain the cornea 206 and prevent tissue necrosis, anadequate level of fluid and nutrient transfer should be maintainedwithin cornea 206. Accordingly, lens body 101 is preferably composed ofa material with a permeability sufficient to allow fluid and nutrienttransfer between corneal tissue 207 adjacent to anterior surface 102 andposterior surface 103, in order to sustain the cornea over a desiredperiod of time. For instance, in one example embodiment lens body 101 iscomposed of a microporous hydrogel material. Microporous hydrogels aredescribed in further detail in U.S. Pat. No. 6,875,232 entitled “CornealImplant and Method of Manufacture,” which is fully incorporated byreference herein.

TABLE 1 depicts example values for one embodiment of a 5.0 millimeter(mm) diameter lens 100 having a given diopter. These example values arefor purposes of illustration only and in no way limit the implantablelens 100 to only these or similar values.

TABLE 1 Diopter +2.25 Lens diameter 112 (mm) 5.00 Corrective diameter114 (mm) 4.90 Posterior radius 107 (mm) 7.50 Center thickness 140 (mm)0.030 Bevel radius 124 (mm) 5.500 Edge radius 126 (mm) 0.025 Edgethickness 130 (mm) 0.010 Edge slope angle 132 (degrees) 50

The values of edge thickness 130, edge radius 126, edge slope angle 132and bevel radius 124 are interdependent and based on the desiredcorrective values, the overall lens diameter 112, the diameter ofcorrective portion 122, and the shape of anterior surface 102 andposterior surface 103. Preferably, a lens diameter 112 in the range ofabout 1-10 mm with a corrective portion diameter 114 of about 0.5 mm orgreater will have an edge thickness less than or equal to about 0.015mm, an edge radius 126 in the range of about 0.001-1 mm, an edge slopeangle 132 between 0 and 90 degrees and a bevel radius 124 in the rangeof about 1-10 mm. These ranges are for illustrative purposes only and inno way limit the embodiments described herein.

It should be noted that the modified edge described herein can be usedwith any type, shape or configuration of implantable lens. For instance,lens 100 can be either a corneal inlay or onlay. Lens 100 can beconfigured to treat any visual impairment including, but not limited to,myopia, hyperopia, astigmatism, and presbyopia. Lens 100 can also beconfigured to treat any combination of visual impairments including, butnot limited to, presbyopia with myopia or hyperopia and presbyopia withastigmatism. The overall outer profile 119 of lens 100 can be any shape,including, but not limited to, circular, elliptical, irregular,multi-sided, and shapes having an inner aperture. Outer edge surface 104can configured with outcroppings such as fixation elements and the like.Also, lens body 101 can be fabricated from one or more differentmaterials having any desired refractive index. Furthermore, as will bedescribed in greater detail below, corrective portion 122 of anteriorsurface 102 can be substantially spherical with or without multiplefocal zones, substantially aspherical with or without multipleaspherical surfaces, or any combination and the like. As used herein,the term substantially is intended to broaden the modified term. Forinstance, a substantially spherical surface does not have to beperfectly spherical, but can include non-spherical variations or errorsand the like to a degree sufficient for implementation.

FIGS. 4-9 are cross-sectional views depicting additional exampleembodiments of lens 100 taken along line 1-1 in region 111 of FIG. 1B.In the embodiment depicted in FIG. 4, corrective portion 122 of anteriorsurface 102 is substantially aspherical. The rate of curvature ofaspherical surfaces typically decreases or increases as the surfaceprogresses outwards towards outer edge surface 104. In this embodiment,the rate of curvature of aspheric surface 122 decreases such that thesurface is flatter near outer edge surface 104 than near apex 105 (notshown). Anterior surface 102 and posterior surface 103 diverge as thesurfaces 102-103 progress radially outwards from apex 105 (not shown)towards interface 123. From interface 123 to interface 125, bevel radius124 preferably converges towards posterior surface 103. Likewise, frominterface 125 to interface 127, edge radius 126 also preferablyconverges towards posterior surface 103.

Beveled portion 124 of anterior surface 102 can be flat or curved or anyother desired shape. For instance, in FIGS. 2C-E, beveled portion 124 isspherically curved, however, it should be noted that any type of curvecan be used. In the embodiment depicted in FIG. 5, beveled portion 124is flat. Likewise, first and second edge surface portions 126 and 128can be flat or curved or any other desired shape. For instance, in FIGS.2C-E, edge radius 126 is substantially spherically curved and secondedge surface portion 128 is curved at a variable rate. In the embodimentdepicted in FIG. 6, first edge surface portion 126 is flat, while in theembodiment of FIG. 7 second edge surface portion 128 is flat. Anycombination of flat and curved surfaces can be implemented. Forinstance, in FIG. 8, beveled portion 124, and first and second edgesurface portions 126 and 128 are all flat. Also, edge surface 104 can beimplemented in any desired manner. For instance, in FIG. 9, edge surface104 is flat and oriented in only the Z direction.

FIG. 10A is a top-down view depicting another example embodiment of lens100 having a ring-like shape. Here, lens 100 includes inner aperture 302and inner edge surface 304. FIG. 10B is a cross-sectional view of theembodiment of lens 100 depicted in FIG. 10A taken along line 2-2. Here,it can be seen that anterior surface 102 also includes inner beveledportion 306 located between corrective portion 122 and inner edgesurface 304. Like outer edge surface 104, inner edge surface 304includes first portion 308 and second portion 310, which, in thisembodiment, are both curved. Beveled portion 306 abuts correctiveportion 122 at interface 305 and first portion 308 abuts beveled portion306 at interface 307. Second portion 310 abuts first portion 308 atinterface 309 and abuts posterior surface 103 at interface 311. Itshould be noted that edge surface 304 and beveled portion 306, like edgesurface 104 and beveled portion 124 described above, can be shaped orconfigured in any manner desired. Lenses 100 of the type depicted inFIGS. 10A-B are described in more detail in U.S. application Ser. No.11/032,913, entitled “Myopic Corneal Ring with Central AccommodatingPortion” and filed Jan. 11, 2005, which is fully incorporated byreference herein.

As mentioned above, lens 100 with the modified edge region as describedherein can also be implemented as a multifocal lens. FIG. 11A is aperspective view depicting an example embodiment of implantable lens 100configured to provide multifocal correction. Here, lens 100 includes twocorrective regions 402 and 404 each having a different refractive index.The different refractive indices in each region allow for correction ofvisual impairments over different distance ranges. For instance, therefractive indices of regions 402 and 404 can be predetermined such thatregion 402 provides refractive correction over relatively near distanceswhile region 404 provides correction over relatively far distances orvice-versa. Any combination and number of two or more corrective regionscan be used. Likewise, any refractive index can be used includingrefractive indices that are substantially similar to cornea 206 (about1.36-1.39) and refractive indices that are greater than or less thanthat of cornea 206.

FIG. 11B is a top down view depicting this embodiment of lens 100 takenalong direction 410. In this embodiment, lens 100 has apex 105, agenerally circular outer edge profile 409 and regions 402 and 404 havediameters 406 and 408, respectively. The transition between regions 402and 404 is referenced as interface 403. Here, regions 402 and 403 arearranged as generally concentric circular regions. It should be notedthat regions 402 and 403 can be arranged in any desired manner such aseccentric, hemispherical, irregular and the like. Also, any number oftwo or more regions can be implemented with any number or none of thoseregions being integrally coupled together.

FIG. 11C is a cross-sectional view depicting the embodiment of FIG. 11Btaken over line 3-3. Here, corrective portion 122 of anterior surface102 is substantially spherical having one radius of curvature 106 andposterior surface 103 is also substantially spherical having one radiusof curvature 107. Adjustment of these radii 106-107 along with theselection of the appropriate refractive index for regions 402-404 canprovide the proper diopter values for each zone to treat a givenindividual. FIG. 11D is an enlarged cross-sectional view of thisembodiment lens 100, showing region 411 of FIG. 11C in greater detail.In this embodiment, similar to the embodiment depicted in FIG. 2D, lens100 includes bevel radius 124, edge radius 126 and curved second edgesurface portion 128.

To provide different refractive indices, in one example embodimentregions 402 and 404 are fabricated from different materials integrallycoupled together at interface 403. For instance, each region 402 and 404can be fabricated from different microporous hydrogel materials. In oneexample embodiment, lens 100 is fabricated by first forming a solidpolymeric cylindrical core 502, such as that depicted in FIG. 12A, whichcorresponds to region 402 and has approximately the same diameter asdiameter 406 of region 402. This core can then be surrounded by amonomeric solution 503 in a manner similar to that depicted in FIG. 12B.Polymeric core 502 is preferably at least slightly soluble in monomericsolution 503. Monomeric solution 503 can then be polymerized to formouter polymeric cylindrical region 504 surrounding inner core 502 asdepicted in FIG. 12C. Outer region 504 preferably corresponds to region404 and has approximately the same diameter or a slightly largerdiameter than diameter 408 of region 404. Inner core 502 and outerregion 504 together form lens core 506, from which one or more lens canbe fabricated, such as, for instance, by separating core 506 intodisc-shaped buttons 508 as depicted in FIG. 12D. Each individual buttoncan be machined or cut into the desired shape and further processed(e.g., softened, hydrated, etc.) to form an individual lens body 101.

As mentioned above, polymeric core 502 is preferably at least slightlysoluble in monomeric solution 503. This is so that solution 503 candissolve the outer surface of core 502 and become interspersed and mixedwith the dissolved portion of core 502. Once solution 503 is polymerizedand solidified, an interface region 505 between cores 502 and 504 can beformed where the different polymers in cores 502 and 504 together forman interpenetrating network. This interface region corresponds tointerface region 430 in FIG. 13 below and integrally couples regions 402and 404 together.

FIG. 13 is a cross-sectional view of an example embodiment of lens 100having interface region 430. By integrally coupling regions 402 and 404together, interface region significantly reduces the risk that regions402 and 404 will separate, such as can be the case when an adhesive isused to join regions 402 and 404. Furthermore, interface region 430 canhave a refractive index or range of refractive indices between therefractive indices of regions 402 and 404. As a result, interface region430 can act as an optical transition between regions 402 and 404 and adda third multifocal region to lens 100. This can eliminate an immediateor sharp transition between the refractive indices of regions 402 and404 that could result in visual artifacts such as halo or glare.

The width 420 of interface region 430 can be varied as desired. Forinstance, to generate a wider interface region 430, monomeric solution504 can be left in contact with inner core 502 for a longer period oftime before polymerization, or, the solubility of inner polymeric core502 in monomeric solution 504 can be increased. Generally, the widerinterface region 430 becomes, the more noticeable region 430 to thesubject as a multifocal region.

It should be noted that lens 100 can be fabricated in any manner and isnot limited to the example described with respect to FIGS. 12A-12D.Other polymerization methods known in the art including, but not limitedto, dip coating, spinning, casting, and the polymerization ofpre-polymers, can be used in the formation of regions 402 and 404.

In another example embodiment, each region 402 and 404 is configuredwith varying levels of permeability. For instance, region 402 can have alevel of permeability to fluid and nutrients that is sufficient tosubstantially sustain cornea 206, while region 404 can have apermeability to either fluid or fluid and nutrients that is relativelyless than region 402, including being entirely impermeable to fluid andnutrients. This allows for the use of more types of materials having awider range of refractive indices and/or structural characteristics.

In order to allow enough fluid/nutrient transfer to sustain cornea 206,the size of any impermeable region is preferably minimized. Forinstance, any circular central region, similar to the embodiment ofregion 402 described with respect to FIG. 11B, that is impermeable tofluid and nutrients is preferably less than about 3 mm in diameter(diameter 406) or about 7.1 square mm. However, it should be noted thatlens 100 is not limited to any one total impermeable surface area, thesize and surface area of any impermeable region being dependent on theshape of the region and the relative level of permeability of anyaccompanying regions. For instance, an example embodiment of lens 100having many concentric regions arranged in a bullseye fashion where theregions alternate between permeable and impermeable could allow for atotal surface area of impermeable regions that is greater than 7.1square mm.

FIG. 14A is a top-down view depicting another example embodiment ofmultifocal lens 100 where corrective portion 122 of anterior surface 102includes surfaces 602 and 604 having different rates of curvature.Surfaces 602 and 604 have diameters 610 and 612, respectively. FIG. 14Bis a cross-sectional view of another example embodiment of lens 100taken along line 4-4 of FIG. 14A. Here, surfaces 602 and 604 are eachsubstantially spherical but have different radii of curvature 605 and606, respectively. The abutment between surface 602 and 604 isreferenced as interface 603. Each surface 602 and 604 can be configuredwith a different diopter value to correct for separate distances ranges(e.g., near-far, far-near, etc.). TABLE 2 depicts example values forthree embodiments of a 5.0 millimeter (mm) diameter lens 100 havingmultiple spherical surfaces 602 and 604 similar to that depicted in FIG.14B. Each of the three embodiments provides for a different degree ofcorrection for relatively far distances (sphere) and relatively neardistances (add). These corrective values are shown in the format “spherediopter/add diopter.” All of these example values are for purposes ofillustration only and in no way limit the implantable lens 100 to onlythese or similar values.

TABLE 2 Parameter 0.00/1.75 0.00/2.00 0.00/2.25 Lens diameter 112 (mm)5.00 5.00 5.00 Posterior radius 107 (mm) 7.50 7.50 7.50 Center thickness140 (mm) 0.020 0.021 0.022 Bevel radius 124 (mm) 4.770 4.770 4.770 Edgeradius 126 (mm) 0.025 0.050 0.050 Edge thickness 130 (mm) 0.010 0.0100.010 Edge slope angle 132 (degrees) 45 45 45 Spherical Surface 602Diameter 610 (mm) 2.00 2.00 2.00 Radius 605 (mm) 7.252 7.217 7.182Spherical Surface 604 Diameter 612 (mm) 4.90 4.90 4.90 Radius 606 (mm)7.505 7.505 7.505

FIG. 14C is a cross-sectional view of another example embodiment of lens100 taken along line 4-4 of FIG. 14A. Here, surfaces 602 and 604 areeach substantially aspherical. Surfaces 602 and 604 each have a radius614 and 616, respectively, measured along central axis 118. Radius 616is measured along central axis 118 from vertex 622 to an imaginaryposition of surface 604 corresponding to the point where surface 604would intersect central axis 118 if surface 604 were to extend all theway to central axis 118 as indicated by dashed line 620.

Because aspherical surfaces are inherently multifocal, the inclusion ofmultiple aspherical surfaces provides an added dimension ofmultifocality to lens 100. For instance, surface 602 can have anyasphericity (Q) and can provide a range of diopter values varying at anyrate from apex 105 to interface 603 and can be configured to provide forcorrection over relatively near distances, while surface 604 can have arange of diopter values varying at any rate from interface 603 tointerface 123 and can be configured to provide correction overrelatively far distances. One of skill in the art will readily recognizethat each surface 602 and 604 can have any range of diopter values andprovide for correction over any distance.

TABLE 3 depicts example values for one embodiment of a 5.0 millimeter(mm) diameter lens 100 having multiple aspherical surfaces 602 and 604similar to that depicted in FIG. 14C. Each of the three embodimentsprovides for a different degree of correction for relatively fardistances and relatively near distances. All of these example values arefor purposes of illustration only and in no way limit the implantablelens 100 to only these or similar values.

TABLE 3 Parameter 0.00/1.75 D 0.00/2.00 D 0.00/2.25 D Lens diameter 112(mm) 5.00 5.00 5.00 Posterior radius 107 (mm) 7.50 7.50 7.50 Centerthickness 140 (mm) 0.020 0.021 0.022 Bevel radius 124 (mm) 4.770 4.7704.770 Edge radius 126 (mm) 0.025 0.025 0.025 Edge thickness 130 (mm)0.010 0.010 0.010 Edge slope angle 132 45 45 45 (degrees) AsphericalSurface 602 Diameter 610 (mm) 2.00 2.00 2.00 Radius 614 (mm) 7.217 7.1827.148 Asphericity (Q) −1.015 −1.001 −0.987 Aspherical Surface 604Diameter 612 (mm) 4.90 4.90 4.90 Radius 616 (mm) 7.452 7.452 7.452Asphericity (Q) −0.225 −0.225 −0.225

Although not depicted in FIGS. 14A-C, lens 100 can have one or moretransition surfaces at interface 603 that provide for a smoothertransition between surfaces 602 and 604, as sharp transitions canstimulate adverse tissue reactions. Edge surface 104 and beveled portion124 are also not depicted in FIGS. 14A-C, but it can be included asdesired. Also, it should be noted that lens 100 can have any number ofmultifocal surfaces or refractive regions as desired. The multifocalsurfaces 602 and 604, substantially spherical or substantiallyaspherical, can also be arranged in any manner desired including, butnot limited to, eccentric, hemispherical, irregular and the like.

FIG. 15 shows an example of an intracorneal inlay 31 implanted in acornea 30. The inlay 31 may have a meniscus shape with an anteriorsurface 32 and a posterior surface 33. The inlay 31 is preferablyimplanted in the cornea at a depth of 50% or less of the cornea(approximately 250 microns or less), and is placed on the stromal bed 35of the cornea created by a micro keratome. The inlay 31 may be implantedin the cornea 30 by cutting a flap 34 into the cornea, lifting the flap34 to expose the cornea's interior, placing the inlay 31 on the exposedarea of the cornea's interior, and repositioning the flap 34 over theinlay 31. The flap 34 may be cut using a laser, e.g., a femtosecondlaser, a mechanical keratome or manually by an ophthalmic surgeon. Whenthe flap 34 is cut into the cornea, a small section of corneal tissue isleft intact to create a hinge for the flap 34 so that the flap 34 can berepositioned accurately over the inlay 33. After the flap 34 isrepositioned over the inlay, the cornea heals around the flap 34 andseals the flap 34 back to the un-cut peripheral portion of the anteriorcorneal surface. Alternatively, a pocket or well having side walls orbarrier structures may be cut into the cornea, and the inlay insertedbetween the side walls or barrier structures through a small opening or“port” in the cornea.

The inlay 31 changes the refractive power of the cornea by altering theshape of the anterior corneal surface. In FIG. 15, the pre-operativeanterior corneal surface is represented by dashed line 36 and thepost-operative anterior corneal surface induced by the underlying inlay31 is represented by solid line 37.

The inlay may have properties similar to those of the cornea (e.g.,index of refraction around 1.376, water content of 78%, etc.), and maybe made of hydrogel or other clear bio-compatible material. To increasethe optical power of the inlay, the inlay may be made of a material witha higher index of refraction than the cornea, e.g., >1.376. Materialsthat can be used for the inlay include, but are not limited to,Lidofilcon A, Poly-HEMA, poly sulfone, silicone hydrogel, and the like.The index of refraction may be in the range of 1.33 to 1.55.

This section discusses the use of small intracorneal inlays havingdiameters that are small in comparison with the pupil for correctingpresbyopia. In the preferred embodiment, a small inlay (e.g., 1 to 2 mmin diameter) is implanted centrally in the cornea to induce an “effect”zone on the anterior corneal surface that is smaller than the opticalzone of the cornea for providing near vision. Here, “effect” zone is thearea of the anterior corneal surface affected by the inlay. Theimplanted inlay increases the curvature of the anterior corneal surfacewithin the “effect” zone, thereby increasing the diopter power of thecornea within the “effect” zone. Distance vision is provided by theregion of the cornea peripheral to the “effect” zone.

Presbyopia is characterized by a decrease in the ability of the eye toincrease its power to focus on nearby objects due to a loss ofelasticity in the crystalline lens with age. Typically, a personsuffering from Presbyopia requires reading glasses to provide nearvision.

FIG. 16 shows an example of how a small inlay can provide near vision toa subject's eye while retaining some distance vision according to anembodiment of the invention. The eye 38 comprises the cornea 39, thepupil 40, the crystalline lens 41 and the retina 42. In this example,the small inlay (not shown) is implanted centrally in the cornea tocreate a small diameter “effect” zone 43. The small inlay has a smallerdiameter than the pupil 40 so that the resulting “effect” zone 43 has asmaller diameter than the optical zone of the cornea. The “effect” zone43 provides near vision by increasing the curvature of the anteriorcorneal surface, and therefore the diopter power within the “effect”zone 43. The region 44 of the cornea peripheral to the “effect” zoneprovides distance vision.

To increase the diopter power within the “effect” zone 43, the smallinlay has a higher curvature than the pre-implant anterior cornealsurface to increase the curvature of the anterior corneal surface withinthe “effect” zone 43. The inlay may further increase the diopter powerwithin the “effect” zone 43 by having an index of refraction that ishigher than the index of refraction of the cornea (n_(cornea)=1.376).Thus, the increase in the diopter power within the “effect” zone 43 maybe due to the change in the anterior corneal surface induced by theinlay or a combination of the change in the anterior cornea surface andthe index of refraction of the inlay. For early presbyopes (e.g., about45 to 55 years of age), at least 1 diopter is typically required fornear vision. For complete presbyopes (e.g., about 60 years of age orolder), between 2 and 3 diopters of additional power is required.

An advantage of the small intracorneal inlay is that when concentratingon nearby objects 45, the pupil naturally becomes smaller (e.g., nearpoint miosis) making the inlay effect even more effective. Furtherincreases in the inlay effect can be achieved by simply increasing theillumination of a nearby object (e.g., turning up a reading light).

Because the inlay is smaller than the diameter of the pupil 40, lightrays 47 from distant objects 46 by-pass the inlay and refract using theregion of the cornea peripheral to the “effect” zone to create an imageof the distant objects on the retina 42, as shown in FIG. 16. This isparticularly true with larger pupils. At night, when distance vision ismost important, the pupil naturally becomes larger, thereby reducing theinlay effect and maximizing distance vision.

A subject's natural distance vision is in focus only if the subject isemmetropic (i.e., does not require glasses for distance vision). Manysubjects are ammetropic, requiring either myopic or hyperopic refractivecorrection. Especially for myopes, distance vision correction can beprovided by myopic Laser in Situ Keratomileusis (LASIK), LaserEpithelial Keratomileusis (LASEK), Photorefractive Keratectomy (PRK) orother similar corneal refractive procedures. After the distancecorrective procedure is completed, the small inlay can be implanted inthe cornea to provide near vision. Since LASIK requires the creation ofa flap, the inlay may be inserted concurrently with the LASIK procedure.The inlay may also be inserted into the cornea after the LASIK proceduresince the flap can be re-opened. Therefore, the small inlay may be usedin conjunction with other refractive procedures, such as LASIK forcorrecting myopia or hyperopia.

A method for designing a small inlay to provide near vision will now bedescribed. FIG. 17 shows a small inlay 49 implanted in the cornea 48 andthe change in the shape of the anterior corneal surface 53 induced bythe inlay 49. In FIG. 17, the pre-implant anterior corneal surface isrepresented by dashed line 52 and the post-implant anterior cornealsurface induced by the inlay 49 is represented by solid line 53. Theinlay 49 does not substantially affect the shape of the anterior cornealsurface in the region of the cornea peripheral to the “effect” zone sothat distance vision is undisturbed in the peripheral 54. In the casewhere a distance corrective procedure is performed prior to implantationof the inlay, the pre-implant anterior corneal surface 52 is theanterior corneal surface after the distance corrective procedure butbefore implantation of the inlay.

The inlay 49 has a finite edge thickness 55. The edge thickness 55 cannot be made zero due to the finite material properties of the inlay. Thefinite edge thickness 55 of the inlay produces a draping effect, asdescribed further below. To minimize the draping effect, the edgethickness 55 of the inlay 49 can be made as small as possible, e.g.,less than about 20 microns. In addition to a finite edge thickness 55,the inlay may have a tapered region (not shown) that tapers downwardfrom the anterior surface 50 of the inlay to the edge 55 of the inlay.The tapered region may be 10-30 microns in length.

In FIG. 17, the portion of the anterior corneal surface directly abovethe inlay is altered by the physical shape of the inlay 49. Because ofthe finite edge thickness 55 of the inlay 49, the anterior cornealsurface does not immediately return to its pre-implant shape for adiameter larger than the physical inlay 49. Eventually, the anteriorcorneal surface returns to the pre-implant corneal surface 52.Therefore, the draping effect produces a drape region 56 that extendsthe shape change of the anterior corneal surface induced by the inlay49.

FIG. 18 illustrates a variety of possible draping shapes 58. FIG. 18shows the radius (d_(I)/2) of an inlay region 59 and the total radius(d_(Z)/2) of the shape change due to the draping effect. The possibledraping shapes 58 are shown in dashed lines, and may depend on factorssuch as the edge thickness, the local mechanical properties of the flapmaterial, the diameter of the inlay (dI), the mechanical properties ofthe inlay material, and other geometric factors. The precise shape ofthe drape can be approximated by invitro or invivo clinical experimentsand/or by complex mechanical modeling using techniques such as finiteelement analysis.

It is useful to define the optical zone diameter (d_(Z)) correspondingto the size of the anterior corneal surface affected by the inlay 49, asshown in FIG. 17. For purposes of the design method, it is sufficient toassume that the relationship between the optical zone and the inlaydiameter, given the other variables, can be determined by the methodsoutlined above.

A method for designing a small inlay to provide near vision according toan embodiment will now be given.

(1) The first step is to determine the maximum optical zone (d_(Z)) thatis an acceptable tradeoff between the near vision improvement and theloss of distance vision. Considerations include the pupil size of thespecific subject or a group of characteristic subjects (e.g., subjectswithin a particular age range) while reading nearby objects and thepupil size for distance viewing, especially at night. In an exemplaryapplication, the inlay is placed in one eye to provide near vision anddistance correction by other means is performed on the fellow eye. Inthis example, both eyes contribute to distance vision, with thenon-inlay eye providing the sharpest distance vision. The eye with theinlay provides near vision.

(2) Given the empirically derived or theoretically derived relationshipbetween the optical zone (d_(Z)) and the inlay diameter (dl),approximate the inlay diameter that achieves the optical zone.

(3) Design the inlay using the method outlined in detail below. Thismethod is similar to the design methods described in U.S. applicationSer. No. 11/293,644, titled “Design of Intracorneal Inlays,” filed onDec. 1, 2005, the entirety of which is incorporated herein by reference.

(4) Finally, use optical ray-trace methods to assess the image qualityof distance and near images with the inlay using the entire cornealsurface (i.e., the corneal surface within the inlay diameter (dl),between the inlay diameter and the optical zone (d_(Z)), and theperipheral to the optical zone). Make small adjustments to the inlaydesign to optimize the distance and near image quality based on theinlay design method outlined below and the predicted drape shape givenby the methods described above.

The design method of step three will now be given.

FIGS. 17 and 18 show two regions affected by the inlay design: a“central region” 57 defined by the inlay diameter (dl), and a “draperegion” 56 falling between the inlay diameter and the optical zone(d_(Z)). The design method described below is used to design inlays toproduce desired shapes of the anterior corneal surface in the centralregion to correct presbyopia. This design method assumes that the inlaymaterial has the same index of refraction as the cornea.

A first step in the design of an inlay in the central region isdetermining a thickness profile that the inlay must induce on theanterior corneal surface to produce a desired anterior cornealcurvature. The desired ADD power needed to provide near focus dictatesthe desired anterior corneal curvature in the central region (FIG. 18).

A first step in determining the thickness profile of the inlay is todetermine an anterior radius of curvature, r′_(a), that provides thedesired refractive change, ΔRx=Rxdist−ADD, where ADD is the desired ADDpower prescribed for near vision and Rxdist is the distance refractionprior to inlay implant. Rxdist is approximately zero diopters foremmetropic individuals, or is equal to the achieved or targetedpost-operative distance refraction after a surgical procedure to correctthe distance ammetropia. The equivalent change in the cornea'srefractive power, ΔK_(equiv), at the anterior surface is given by:

$\begin{matrix}{{\Delta K_{equiv}} = {\frac{1}{{1/{Rxdist}} - V} - \frac{1}{{1/{ADD}} - V}}} & {{Equation}\mspace{14mu} 1}\end{matrix}$

where V is a spectacle vertex distance, e.g., 0.012 meters, from aspectacle to the cornea's anterior surface. The spectacle vertexdistance, V, takes into account that measurements of the cornea'srefractive power are typically taken with a spectacle located a distancefrom the cornea's anterior surface, and translates these powermeasurements to the equivalent power at cornea's anterior surface.

The pre-implant refractive power at the anterior corneal surface may beapproximated by Kavg−Kpost, where Kavg is the average corneal refractivepower within approximately the optical zone created by the inlay andKpost is a posterior corneal refractive power. The desired radius ofcurvature, r′_(a), of the anterior surface may be given by:

$\begin{matrix}{r_{a}^{\prime}{= \frac{\left( {{{1.3}76} - 1} \right)}{\left( {{Kavg} - {Kpost} + {\Delta K_{equiv}}} \right)}}} & {{Equation}\mspace{14mu} 2}\end{matrix}$

For purposes of design and analysis, Kpost may be approximated as −6diopters. The pre-implant radius of curvature, r_(preimplant), may beapproximated by:

r _(preimplant)=(1.376−1)/(Kavg−Kpost)  Equation 3

The two radii of curvature need not originate from the same origin.

FIG. 19 shows a cross-sectional view of a thickness profile 60 specifiedby a difference between the desired anterior corneal surface 62 and thepre-implant anterior corneal surface 61. In FIG. 19, arrows 63 pointingfrom the pre-implant anterior surface 61 to the desired anterior surface62 represent the axial thickness, L(r), of the thickness profile 60 atdifferent positions along an r axis that is substantially perpendicularto an optical z axis. The double arrow 64 represents a center thickness,L_(c), of the thickness profile. In this embodiment, the thicknessprofile 60 is rotationally symmetric about the z axis. Thus, the entirethickness profile may be defined by rotating the cross-sectional viewshown in FIG. 19 about the z axis.

The thickness L(r) of the thickness profile may be given by:

L(r)=+Z _(preimplant)(r;r _(preimplant))−Z _(anew)(r;r′ _(a)) and

L _(c) =z _(anew)(d _(t)/2)−Z _(preimplant)(d _(t)/2)  Equation 4

where L_(c) is the center thickness of the thickness profile,Z_(implant)(r) is the pre-operative anterior corneal surface as afunction of r, Z_(anew) (r) is the desired anterior corneal surface as afunction of r, and d_(I) is the diameter of the inlay. In the exampleabove, the anterior surfaces Z_(anew) and Z_(preimplant) were assumed tobe spherical. This need not be the case. The anterior surfaces may alsobe aspheric. More generally, the desired anterior surface Z_(anew) maybe a function of desired ADD and also more complex design parameters,e.g., an aspheric surface for higher-order aberration correction. Also,the pre-implant anterior surface Z_(preimplant) is generally aspheric.For designs requiring aspheric surfaces, the surface function Z(r) maybe given by the general aspheric form:

$\begin{matrix}{{Z(r)} = {\frac{r^{2}/r_{c}}{1 + \sqrt{1 - {\left( {1 + k} \right)\left( {r/r_{c}} \right)^{2}}}} + {a_{4}r^{4}} + {a_{6}r^{6}}}} & {{Equation}\mspace{14mu} 5}\end{matrix}$

where: r_(e) is the radius of curvature

-   -   k is a conic constant    -   a₄ and a₆ are higher order aspheric constants        For a spherical surface, k=0, a₄=0, and a₆=0. The human cornea        may be approximated by k=−0.16, a₄=0 and a₆=0. The radius of        curvature, r_(e), may be specified by the ADD power for        correction of presbyopia, and the other parameters may specify        corrections for higher-order aberrations.

The above expressions for the thickness profile are intended to beexemplary only. Other mathematical expressions or parameters may be usedto describe similar or other thickness profiles. Therefore, theinvention is not limited to particular mathematical expressions orparameters for describing the thickness profile.

After the required thickness profile L(r) is determined, the inlay isdimensioned to have substantially the same thickness profile. Theprofiles should have the same thickness to within about one micron,which would cause a diopter difference of about one eight of a diopterif the center thickness differs by one micron. An eighth of a diopter ishalf the accuracy with which ophthalmic refractive errors are manuallyrecorded. Next, the thickness profile of the inlay is increased by thefinite edge thickness (h_(edge)) by the manufacturing process. Thisfinite edge thickness is one factor inducing the drape as illustrated inFIG. 18. When implanted in the cornea, the thickness profile of theinlay is substantially transferred to the anterior corneal surfacethrough the intervening flap, thereby producing the desired post-implantanterior corneal surface in the central region. The draping effectcauses the change in the anterior corneal surface thickness to extendbeyond the central region. This draping effect can be minimized, e.g.,by reducing the finite edge thickness of the inlay as much as possible.

The design method above assumed that the index of refractive of theinlay is the same as the cornea, in which case changes in refractivepower of the cornea is due solely to the change in the anterior cornealsurface induced by the inlay. An inlay with intrinsic power (e.g., ahigher index of refraction than the cornea) may also be used, in whichchanges in the refractive power is provided by a combination of thephysical inlay shape and the intrinsic power (i.e., index of refraction)of the inlay. Design methods for inlays with intrinsic power aredescribed in application Ser. No. 11/381,056, titled “Design of Inlayswith Intrinsic Diopter Power,” filed on May 1, 2006, the entirety ofwhich is incorporated herein by reference.

For some applications, it is desirable for an inlay to induce aneffective optical zone on the anterior corneal surface that is muchlarger than the inlay diameter. The increase in the effective opticalzone allows the inlay to produce a much larger clinical effect on thepatient's vision than the actual inlay diameter. In one example, a 1.5mm-2 mm range diameter inlay has an increased effective optical zone of4 mm-5 mm, in which the optical effect of the inlay is 2× to 3× greaterthan its diameter. The increased effective optical zone can also beachieved with inlay diameters outside the above range. For example, thediameter of the inlay may go down to 1 mm or less for some designs,while achieving the desired optical effect.

The increase in the effective optical zone (i.e., “effect” zone) of theinlay can be achieved by increasing the draping effect of the inlay.Increasing the draping effect extends the drape region, and thereforethe effective optical zone (i.e., the area of the anterior cornealsurface affected by the inlay). The draping effect may be increased,e.g., by increasing the finite edge thickness of the inlay so that theanterior corneal surface returns to its pre-implant surface at a largerradius.

Small diameter inlays inducing effective optical zones much larger thanthe inlay diameter may be used to correct hyperopia. For example, aninlay with a diameter of 2 mm can provide increased diopter power overan effective optical zone having a diameter of 4 mm. The curvature ofthe anterior corneal surface in the drape region is greater than thepre-implant anterior corneal surface. Therefore, the draping effectextends the area of the anterior corneal surface where the curvature isincreased, thereby extending the effective optical zone of the inlay andproviding increased diopter power over a wider diameter than the inlaydiameter. This increase in the effective optical zone allows for thecorrection of hyperopia using smaller diameter inlays.

An inlay with increased effective optical zone may also be used tocorrect various vision impairments including presbyopia, hyperopia,myopia, and higher order aberrations. In the case of presbyopia, asufficient “effect” zone may be achieved with an even smaller diameterinlay. For example, a 1 mm diameter inlay may be used to produce a 2 mmdiameter “effect” zone.

Clinical data will now be presented in which the effective optical zoneinduced by an inlay is larger than the inlay diameter. In general,topographic instruments can be used to measure the change in theanterior surface elevation induced by an inlay, calculate the change inthe anterior surface curvature and deduce the change in the diopterpower. FIG. 20 shows an example of a 3D topographic difference mapshowing the change in the anterior corneal surface for a subject(subject 1) between a preoperative examination and a one weekpostoperative examination. In this example, an intracorneal inlay wasimplanted in subject 1 having a diameter of 2 mm, a center thickness ofapproximately 36 microns, and an edge thickness of approximately 30microns. The inlay was placed under a corneal flap created using a laserkeratome (by Intralase, Inc.) at a depth of approximately 110 microns. AScheimpflug topographer (“Pentacam” by Oculus, Inc.) was used to measurethe surfaces. From FIG. 20, it is clear that the implanted inlaysteepened the anterior corneal surface.

FIG. 21 shows the average radial elevation profile calculated from datain FIG. 20. Average radial profiles for two additional subjects(subjects 2 and 3) who received the same inlay design are also shown.Note that the central anterior surface elevation change was less thanthe center thickness of the inlay. This reflects biomechanicalinteractions between the inlay material, stromal bed on which it restsand the overlying keratometric flap. However, in all cases the inlayincreased the anterior surface elevation beyond the physical diameter ofthe inlay. FIG. 21 suggests that the effective optical zone induced bythe inlay was approximately twice the inlay diameter for this particulardesign. Inlays with different diameters, center thicknesses andthickness profiles may have different “effect” zone sizes.

FIG. 22 shows a contour map of the refractive change induced by theintracorneal inlay. This is calculated from the elevation differences bycalculating the sagittal curvature map and converting to diopter powerusing:

Diopter power=(n _(c)−1)/sagittal curvature

where n_(c) is the index of refraction of the cornea. Again, theeffective optical zone of the inlay was greater than the diameter of theinlay.

In some embodiments the inlay has a diameter between about 1 mm andabout 3 mm, and in some particular embodiments the inlay is about 2 mmin diameter. In some embodiments the inlay central thickness (fromanterior to posterior surfaces) is about 20 microns to about 40 microns,while in some particular embodiments the inlay central thickness isabout 30 microns, and in some more particular embodiment the centralthickness is about 32 microns. In some embodiments the inlay has an edgethickness of about 3 microns to about 16 microns, and in some particularembodiments the edge thickness is about 12 microns. In some embodimentsthe anterior surface radius of curvature is about 7 mm to about 13 mm,and in some particular embodiments the anterior surface radius ofcurvature is about 10 mm. In some embodiments the posterior surfaceradius of curvature is about 5 mm to about 12 mm, and in some particularembodiments the posterior surface radius of curvature is about 8.5 mm.

In one particular embodiment the inlay has a diameter of about 2 mm, thecentral thickness is about is about 32 microns, the edge thickness isabout 12 microns, the anterior surface radius of curvature is about 10mm, and the posterior surface radius of curvature is about 8.5 mm.

In some embodiments the diameter of the inlay is less than 4 mm.

Exemplary embodiments have been shown and described herein. It will beobvious to those skilled in the art that such embodiments are providedby way of example only. Numerous variations, changes, and substitutionswill now occur to those skilled in the art without departing from thatwhich is described herein.

What is claimed is:
 1. A method of manufacturing a corneal implant,comprising: creating an implant body that has a meniscus shape, adiameter of 2.5 mm or less, and an index of refraction of 1.376.